Surface protection of exposed biological tissues

ABSTRACT

The invention relates to a biodegradable barrier network comprising at least two macromolecular substances, one being anionic and the other one cationic. The invention also relates to applicators and kits comprising components to be used to create said biodegradable barrier network. The invention also relates to the use of said applicator or kit in therapy, such as in medicine, veterinary medicine and horticulture.

This application is a Continuation-in Part of U.S. Ser. No. 12/822,809 filed Jun. 24, 2010, which is a Divisional of U.S. Ser. No. 10/585,159, filed 19 Apr. 2007, which is a National Stage Application of PCT/SE2004/002016, filed 23 Dec. 2004, which claims benefit of Ser. No. 0303588-8, filed 30 Dec. 2003 in Sweden and U.S. Ser. No. 60/606,130, filed 1 Sep. 2004 and which applications are incorporated herein by reference. A claim of priority is made to each of the above disclosed applications.

FIELD OF INVENTION

The invention relates to a biodegradable barrier network comprising two polypeptides, one being anionic and the other one cationic. The invention also relates to applicators and kits comprising components to be used to create said biodegradable barrier network. The invention also relates to the use of said applicator or kit in therapy, such as in medicine, veterinary medicine and horticulture.

BACKGROUND OF INVENTION

Tissue surfaces need protection depending on the type and extent of chemical exposure and wearing that they normally are subjected to. All cells in the body are thus covered by a cell membrane bilayer that mainly consists of lipids and proteins. Epithelial surfaces, which connect to the exterior world; the respiratory, gastrointestinal, and to some extent also the genitourinary tracts, are exposed to a rather harsh environment. These epithelial surfaces are further covered by a mucus layer having viscoelastic and pronounced protecting properties. Tissues such as synovia and mesothelium, on the other hand, are not protected by mucus since they are not exposed to drastic condition of the same magnitude.

In addition, the vital epithelial tissues, such as blood vessels or blood organs, are coated with mucous, serous, synovial and endothelial membranes so that they can function independently of each other. The peritoneal, pericardial and pleural membranes consist of a single layer of mesothelial cells, which is covered by a thin film of peritoneal fluid. The components of the membranes as well as the covering layer of fluid have several functions, e.g. lubrication of the enclosed organs.

The protective epithelial membrane is very thin and comprises a delicate layer of connective tissue covered with a monolayer of mesothelial cells and only one or a few bilayers of phospholipids. This makes the synovia and mesothelium tissue especially vulnerable to infection and trauma. When such a membrane is exposed to a physical, chemical or microbial challenge, many potent substances, which are harmful to the membrane, are often released in response thereto. The structure and function of the membrane is consequently easily destroyed in connection with trauma, ischemia, and infection. After an irritation of the stress-sensitive membrane, e.g. only by the desiccation or abrasion of the membrane surfaces during surgery, it will rapidly be covered with a fibrin clot. Since the plasminogen activating activity (i.e. the fibrinolytic capacity) is reduced after trauma, the fibrin clots will later on become organised as fibrous adhesions, i.e. small bands or structures, by which adjacent serous or synovial membranes adhere in an abnormal way. Surgical operations, infection or inflammation in those parts of the body, which are coated with serous or synovial membranes, can result in adhesive inflammation regardless of the size of the affected area. The adhesions between vital epithelial tissues are formed within the first few days following surgery trauma or infection and may be observed not only in particular portions of the body but in all vital tissues. Such adhesions between for example contact zones between intestines or between intestines and the abdominal wall are the result of the often unnoticed tissue damage as desiccation and they occur for various reasons, including mechanical and chemical stimulation of vital tissues accompanying surgical manipulations, postoperative bacterial infection, inflammation or further complications. Adhesion of vital epithelial tissues, large or small, may be observed in most surgical fields. It has been reported that of all patients undergoing abdominal surgery at one hospital over a four-year period, 93% were found to have adhesions from previous operations. In addition, in a 10 year period there will be a need of adhesion prevention in about 20% of all surgical operations, which corresponds to more than 1 million operations annually on each major continent.

However, the obtained postsurgical adhesions are the result of a natural wound healing response of tissue damage occurring during surgery. Numerous factors play a role in peritoneal wound healing and the development of adhesions. Among others are peritoneal macrophages known to have an important role in initial peritoneal repair. Thus, while waiting after surgery for the body to produce new protective layers it is desired to supply the corresponding protection from the outside to exposed epithelial surfaces in an effective way. Furthermore, it is important to prevent or reduce the infection and/or the inflammation obtained after surgery as well as the accompanying fibrin formation.

Various bioactive materials and macromolecules have been reported to decrease the extent of postoperative abdominal adhesions. Likewise, a number of methods for limiting the formation of surgical adhesion have been studied with some encouraging but often ambiguous results. However, most efforts made to avoid or reduce postoperative peritoneal adhesions have finally been abandoned. Among the methods used prevention of fibrin formation, reduction of fibrin formation, surface separation, and surgical techniques can be mentioned.

Numerous investigations have been carried out in which barriers are placed at a site of injury in order to prevent fibrin bridge formation between the injured tissue and neighboring organs. Such barriers include resorbable materials, such as enzymatically degradable oxidized regenerated cellulose, and slowly dissolving physiochemically crosslinked hydrogels of the Pluronic™ type.

Most methods of surface protection of exposed epithelial surfaces, whereby a postsurgical adhesion formation is limited, have also focused on providing wound separation by placing a material between the tissues. In addition, several types of viscous polymer solutions such as polyvinylpyrrolidone, sodium carboxymethyl cellulose, dextrans, and hyaluronic acid have been added before and/or at the end of surgery in order to control the wound healing events after the occurrence of the presumed tissue injuries. These solutions are supposed to act by increasing the lubrication and preventing the fibrin clots from adhering to other surfaces or by mechanically separating damaged tissues while they heal.

The employed polymeric solutions are mainly based on the viscosity of the high molecular weight polymer, which is intended to increase with increasing concentration. The polymer is often a polysaccharide as in U.S. Pat. No. 4,994,277, in which a viscoelastic gel of biodegradable xanthan gum in a water solution for preventing adhesions between vital tissues is described. However, the major disadvantage of these polymers, when used for reducing for example peritoneal adhesions as protective coatings during surgery or surface separation agents after surgery, is that they do not significantly reduce adhesions because of their short residence time in the peritoneal cavity. The result is that subsequent surgeries have to be performed on the patient. Less viscous polymer solutions have been used as a tissue protective coating during surgery in order to maintain the natural lubricity of tissues and organs and to protect the enclosing membrane. Precoating for tissue protection and adhesion prevention includes coating tissues at the beginning of surgery before a significant tissue manipulation and irritation can occur and continuously throughout the operation so that a protective coating can be maintained on the tissues.

U.S. Pat. No. 5,366,964 shows a surgical viscoelastic solution for promoting wound healing, which is used in direct contact with cells undergoing wound healing. The solution is intended for cell protection and cell coating during surgery and comprises one or several polymeric components. Hydroxypropylmethyl cellulose and chondroitin sulphate are supposed to lubricate the tissue, while sodium hyaluronate would provide viscoelastic properties to the solution. Several agents of today for treating postsurgical adhesions contain hyaluronic acid. For example U.S. Pat. No. 5,409,904 describes solutions which reduce cell loss and tissue damage intended for protecting endothelial cells during ophthalmic surgery. The compositions used are composed of a viscoelastic material comprising hyaluronic acid, chondroitin sulphate, modified collagen, and/or modified cellulose. In WO 9010031 a composition is described for preventing tissue adhesion after surgery containing dextran and hyaluronic acid in which the substances are supposed to act synergistically. In WO 9707833 a barrier material for preventing surgical adhesions is shown, which comprises benzyl esters or covalently crosslinked derivatives of hyaluronic acid. A hyaluronic acid based agent manufactured by Pharmacia under the trademark Healon and originally intended as an intraocular instillation has been found to be the most effective agent up to now. However, hyaluronic acid is isolated from cock's crests and is thus very expensive as well as potentially allergenic even in small quantities and even more for large surfaces such as the peritoneum which has an area of about two m².

In WO 9903481 a composition for lubricating and separating tissues and biological membranes from adjacent membranes or adjacent cells or tissues is shown, which comprises a hydrophobic polymer formed from a biologically acceptable water-soluble cationic polymer carrying covalently bound hydrophobic groups. Likewise, water-insoluble biocompatible compositions are shown in EP 0,705,878, which comprise a polyanionic polysaccharide combined with a hydrophobic bio-absorbable polymer.

In U.S. Pat. No. 6,235,313 a variety of polymers were compared for adhesive force to mucosa surfaces. Negatively charged hydrogels, such as alginate and carboxymethyl cellulose, with exposed carboxylic groups on the surface, were tested, as well as some positively-charged hydrogels, such as chitosan. The choice was based on the fact that most cell membranes are actually negatively charged. However, there is still no definite conclusion as to what the most important property is in order to obtain good bioadhesion to the wall of the gastrointestinal tract. For example, chitosan is considered to bind to a membrane by means of ionic interactions between positively charged amino groups on the polymer and negatively charged sialic acid groups on the membrane. Thus, polycationic molecules, such as chitosan and polylysine, have a strong tendency to bind to exposed epithelial surfaces since these generally have a negative net charge.

A main drawback of both these cationic molecules is that they exhibit toxic effects. For example, polylysine is considered to act as an inhibitor of the calcium channel by producing a conformational change, thereby inhibiting transmembrane ion fluxes.

SUMMARY OF THE INVENTION

The invention relates to a new invented biodegradable barrier network, which is non-toxic, which is possible to produce at low cost, biodegradable and non-allergenic. Such a network enables the possibility to treat postsurgical adhesions in an efficient way.

First, the invention relates to a biodegradable barrier network comprising a positively charged macromolecular substance and a negatively charged macromolecular substance including and applicator and kit for administering said positively charged macromolecular substance and negatively charged macromolecular substance to form the barrier network.

Secondly, the invention relates to an biodegradable barrier network comprising a cationic polypeptide, an anionic polypeptide and a pharmaceutically acceptable carrier.

Thirdly, the invention relates to an applicator comprising a cationic polypeptide and a pharmaceutically acceptable carrier, an anionic polypeptide and a pharmaceutically acceptable carrier, said cationic and anionic peptide being separated from each other by a separator.

Fourthly the invention relates to a kit comprising a cationic polypeptide and a pharmaceutically acceptable carrier an anionic polypeptide and a pharmaceutically acceptable carrier and means for administering said cationic and anionic polypeptide.

Finally the invention relates to a method of treating a mammal having an injury, comprising use of the applicator or the kit according to the invention to create the biodegradable barrier network according to the invention.

By providing such a network, applicator and kits a new improved product will be available on the market to be used in wound healing.

BRIEF DESCRIPTION OF FIGURES

FIG. 1 is a schematic of an embodiment of the biodegradable barrier network.

FIGS. 2A and B show the effect of the biodegradable barrier network at the site of an injury. Visual adhesion was observed at the site of injury with no barrier network (FIG. 2A). No adhesion and healed surface was observed at the site of injury with a barrier network (FIG. 2B).

FIGS. 3A and B show the biodegradability of the barrier network. FIG. 3A shows the biodegradable barrier network at the site of injury immediately after administration. After 4 weeks, the barrier network is degraded and not remains of the barrier network are observed (FIG. 3B).

FIG. 4 is a graphical representation showing the effect of concentration on adhesion.

FIG. 5 is a graphical representation showing the effect of variation of net charge and density on adhesion.

DETAILED DESCRIPTION OF THE INVENTION Definitions

In the context of the present invention the following definitions apply:

The term “biodegradable barrier network” is intended to mean a barrier, which prevent adhesion between tissues at an injury and to provide protection of an injured tissue against for example inflammation and infectious agents. Additionally the barrier is degradable over time during the healing process of the injury.

The “network” is intended to mean a network formed between a mixture of at least two macromolecules, such as polypeptides, where at least one of the macromolecule is positively charged (cationic) and the other macromolecule is negatively charged (anionic).

A “macromolecule” is a large complex molecule, such as nucleic acids, proteins, carbohydrates, polypeptides, polelectrolytes, and lipid, having a relatively large molecular weight. In embodiments, the macromolecule comprises at least 1,000 Da. Macromolecule includes polymers made of monomers linked together, including for example, nucleic acids and proteins.

The “same type of amino acid residue” is intended to mean that amino acid residues in a polypeptide is for example solely H (H-H-H-H-H-H-H).

In the present context, amino acid residue names are used as defined by the Protein DataBank (PNB) (www.pdb.org), which is based on the IUPAC nomenclature (IUPAC Nomeclature and Symbolism for Amino Acids and Peptides), Eur J Biochem., 138, 9-37 (1984) together with their corrections in Eur J Biochem., 152, 1 (1985). The term “amino acid” is intended to indicate an amino acid from the group consisting of arginine (Arg, or R), histidine (His or H), lysine (Lys or K), aspartate (Asp or D) and glutamate (Glu or E)

The Biodegradable Barrier Network

The invention relates to a biodegradable barrier network. The biodegradable barrier network being produced at sites of injury. Injured surfaces have a higher negative charge than uninjured surfaces. An electrostatically induced biodegradable barrier network, or precipitate, can be formed at the injured surface by attaching a positively charged macromolecular substance to the injured surface and then adding a negatively charged macromolecule substance to the positively charged macromolecular substance to produce an electrostatically induced biodegradable barrier network (precipitate) comprising the two macromolecules. In this context the term biodegradable barrier network and precipitate are interchangeable in meaning. The biodegradable barrier network formed at the site of injury is a mechanical barrier that protects the surface when healing, by separating injured surfaces from each other, thus preventing adhering of the injured surfaces together. In embodiments, the macromolecules selected for the biodegradable barrier network are polypeptides, which are known to be biodegradable. Cationic polypeptides include lysine, arginine, and histidine. Anionic polypeptides include aspartate, glutamate, asparagine, and glutamine. In embodiments, the positively or negatively charged macromolecular substance comprises a protein. Examples of cationic proteins include proteins include lysozyme, histone proteins, and cytochrome C. Examples of anionic proteins include polyglutamate, albumins, insulines, calcitonine, and parathryoideahormone. In an embodiment, the positively charged macromolecular substance comprises lysozyme, histone proteins, cytochrome C, chitosan, polyallaylamine, or polyquaternium. In an embodiment, the negatively charged macromolecular substance comprises polyglutamate, albumins, insulines, calcitonine, parathryoideahormone, xanthan gum, polacrylate, poly(aromatic sulfonates), poly (aliphatic sulfonates), DNA, RNA aliginic acid, pectin, gum Arabic, or gum karaya.

FIG. 1 shows a schematic of barrier network 1 formation on an injured surface 5. The cationic macromolecule 10 is attached to the negatively charged injured surface 5. The anionic macromolecule 15 interacts with the cationic macromolecule to form an electrostatically induced barrier network 1 at the injured surface 5. The biodegradable barrier network prevents adhesion after surgical procedures and was found to be effective in animal models. The barrier network is biocompatible and does not affect the healing process or immunological functions, or interact with coagulation. As shown in FIGS. 2A and B, the biodegradable barrier network protects injured surfaces during the healing process by preventing adhesions (FIG. 2B). The barrier network can be used when moderate bleeding occurs and when infections are present. The barrier network can also be used to prevent adhesion reformation after adhesiolysis and can be applied during surgery with spray administration.

The biodegradable barrier network comprises electrostatic layering of more than one macromolecule. A solid, thick mechanical barrier is formed through electrostatic layering of multiple macromolecules. In contrast to the multi-component barrier networks of the invention, single component networks do not form a barrier network and the injured surface is only protected by a monolayer of one marcromolecule. The barrier networks of the invention form a mechanical barrier resulting in a solid and thick protection of the injured surface. Due to the electrostatically induced formation of the protective biodegradable barrier network of the invention, the network comprises a higher tendency to form a protection on the injured surfaces compared to the non-injured surfaces. The injured surfaces are more negatively charged then the non-injured surfaces which allows for targeting of the protective barrier network to the injured portions of the surface.

A medium, such as a pharmaceutically acceptable carrier or diluent, is generally used for administration of the macromolecules and formation of the barrier network at the site of injury. The macromolecules form an insoluble precipitate (e.g., a barrier network) when a solution of the positively charged macromolecules is mixed with a solution of the negatively charged macromolecules. Association of oppositely charged macromolecules in an aqueous environment is driven by the entropic gain from release of the counter ions of the respective charged molecules. The driving force for formation of the insoluble precipitate can thus be directly related to the net charges, which provides the number of counter ions available to be released, as well as the charge densities of the oppositely charged macromolecules. A net charge of 3 of each oppositely charged macromolecule, allowing 3 monovalent counter ions to be released, is generally the minimum charge required for strong association of the macromolecules. The charge density cannot be too low for an efficient association to take place. Therefore, the net charge of the respective macromolecules is typically least 3 and the charge density is typically at least 1 elementary charge per 3 times the Debye length. In embodiments, the Debye length is about 1 nm.

For the resulting precipitate/network to be insoluble, the precipitate is neutralized. This neutralization is predominately by the combination of the two macromolecules rather than by small counter ions. Thus, the formation of the insoluble precipitate is promoted by use of oppositely charged macromolecules of similar charge densities. Accordingly, one condition for the formation of the insoluble precipitate is that the macromolecules are sufficiently charged in the medium used for administration so that the macromolecules and medium together form a precipitate at the site of injury (FIG. 1). “Sufficiently charged” as used herein means that the net-charge in combination with the charge density of each macromolecule in the medium used for administration results in an electrostatic attraction between the oppositely charged macromolecules inducing precipitation, which renders the macromolecules insoluble in the medium used for administration.

In embodiments, the net-charges of the separate positively charged and negatively charged macromolecules are cancelled or reduced when the macromolecules are combined resulting in the formation of an insoluble precipitate which is predominantly hydrophobic. The opposite net-charges of the macromolecules, such as polypeptides, cancel each other and result in a biodegradable barrier network due to the hydrophobic nature of the charge neutralized complex. A sufficient charge density for the formation of an insoluble precipitate can be formed by using polypeptides composed of a combination of positively charged amino acids, negatively charged amino acids, and neutral amino acids. Cationic polypeptides include lysine, arginine, and histidine. Anionic polypeptides include aspartate, glutamate, asparagine, and glutamine. Neutral amino acids include glycine, alanine, valine, leucine, isoleucine, tyrosine, tryptophan, phenylalanine, proline, cysteine, and methionine.

As described herein, the lower limit of the charge density for the formation of an insoluble precipitate is related to the Debye length. In embodiments, the charge density is such that the distance between charges on the macromolecule is about 3 times or less the Debye length. In a system where the ionic strength corresponds to an isotonic solution, the Debye length is preferably about 1 nm. In an embodiment, the distance between charges on the macromolecule is about 3 nm or less for efficient formation of the biodegradable barrier network, which corresponds to approximately 10 mol % charged monomers on a mixed polypeptide.

In an embodiment, a stable macromolecule multilayered network can be prepared from pure aqueous solutions above a critical linear charge density of λ_(c)≈0.036 Å⁻¹ by self-assembling nearly random cationic copolymers [DADMAC_(x)-stat-NMVF_(1−x)] of various composition with the strongly charged polyanion PSS. The critical charge density is dependent on the solvent used and the intrinsic properties of the macromolecule used to form the network.

In an embodiment, an insoluble aggregate network can be formed in a macromolecule system such as, for example, the highly charged polycation poly (diallyll-dimethyl-ammoniumchloride) (PDADMAC) and the anionic macromolecule poly (acrylamide-co-sodium acrylate). The formation of the insoluble aggregate network is independent of charge density when the charge density is varied from 10 mol % to 30 mol %. At charge densities above about 10 mol % the formation of an insoluble aggregate network is independent of charge density.

In an embodiment, polylysine and polyglutamate can be used as oppositely charged macromolecules. Both of these macromolecules have charge densities of about 100 mol %. A mix of these two macromolecules/polypeptides generally forms an insoluble precipitate. Preferably, lower limit of charge density is in the order of about 10 mol %.

In an embodiment, a cationic polypeptide consisting of about 10-100 mol % of cationic amino acids, such as lysine, arginine, histidine, or a combination thereof, and about 0-90 mol % of neutral amino acids, such as glycine, alanine, valine, leucine, isoleucine, tyrosine, tryptophan, phenylalanine, proline, cysteine, methionine, or a combination thereof, and an anionic polypeptide consisting of about 10-100 mol % of anionic amino acids, such as aspartate, glutamate, asparagine, glutamine, or a combination thereof and about 0-90 mol % of neutral amino acids, such as glycine, alanine, valine, leucine, isoleucine, tyrosine, tryptophan, phenylalanine, proline, cysteine, methionine, or a combination thereof, are used to prepared a barrier network. When these polypeptides are mixed together an insoluble precipitate is formed. The insoluble precipitate functions as a barrier and prevents adhesions at the site of an injury.

The molecular weight of macromolecules used to form the biodegradable barrier network is not limited. However, limitations such as the slower diffusion rate of larger marcomolecules can negatively affect the efficient formation of the barrier network. In embodiments, the macromolecules comprise a molecular weight of about 1000 Da to about 25,000 kDa. For example, it has been found that poly-L-lysine of MW of about 5 to about 140 kDa in combination with poly-L-glutamate of the corresponding molecular weight efficiently forms a precipitate.

The insoluble precipitate (e.g., the biodegradable barrier network) is formed at the site of injury where it can be visualized and protects the surfaces during healing. Preferably, the biodegradable barrier network is present at the injured surface for at least seven days, which is generally the number of days required for healing, and biodegradables within less than about four weeks from application to the site of injury. FIGS. 3A and 3B shows a biodegradable barrier network according to the disclosure at the site of an injury. As shown in FIG. 3A, the biodegradable barrier network is visible immediately after administration at the injured surface. As shown in FIG. 3B, the barrier network is degraded after 4 weeks and no remains of the barrier network is observed.

At least one of the positively or negatively charged macromolecules may be linked to at least one different neutral macromolecule, peptide or other substance, such as a substance which cleans the injured surfaces, provides antioxidants, modulates apoptosis, promotes healing, inhibits fibrogenesis and tumor growth, controls bleeding, inhibits inflammation, increases stability or protects against infection. Examples are antimicrobial agents, antixoidants anti-inflammatory agents, apoptosis modulators, healing agents, fibrogenesis inhibitors, antitumor agents and antibleeding agents.

Accordingly, the macromolecules may be modified by amidation, esterification, acylation, acetylation, PEGylation or alkylation.

In an embodiment, the network comprises a cationic polypeptide, an anionic polypeptide, and a pharmaceutically acceptable carrier. The network, comprising a cationic polypeptide an anionic polypeptide and a pharmaceutically acceptable carrier. The network, being formed by applying at least one anionic and at least one cationic polypeptide in sequence to a tissue. The cationic polypeptide carrier gelled in order to focus its administration. The tissue being injured and the protecting membrane party or totally removed. Thereby the underlying tissue being exposed and the network will serve as protection of the exposed epithelian surfaces of a mammal, such as humans or animals. The cationic polypetide may be selected from the group consisting of amino acid residues R, H, K, synthetic and semisynthetic variants and mixtures thereof, such as being a poly-lysine, poly-arginine or poly-histidine. The polypeptide may be in the L form. The polypeptide may be a polypeptide consisting of one and the same amino acid residue, such as R-R-R-R or H-H-H-H or a mixture thereof, such as R-H-R-R-H etc. One or more synthetic or semisynthetic amino acid residues may also be present in the polypeptide. The cationic polypeptide may also comprise a mixture of the above mentioned amino acid residues in combination with neutral amino acid residues.

The anionic polypeptide may be selected from the group consisting of the amino acid residues D, E, synthetic and semisynthetic variants, such as being a poly-glutamate or poly-aspartate. The polypeptide may be in the L-form. The polypeptide may be a polypeptide consisting of one and the same amino acid residue, such as D-D-D-D or E-E-E-E or a mixture thereof, such as D-D-E-D-E. One or more synthetic or semisynthetic amino acid residues may also be present in the polypeptide. The anionic polypeptide may also comprise a mixture of the above mentioned amino acid residues in combination with neutral amino acid residues.

The length of the polypeptides may be the same or different, depending on where the biodegradable barrier network should be formed, i.e., depending on which tissue it should be applied to. The size may be at least 1.000 Da, such as between about 5.000 to about 50.000 Da or even up to 100.000. Examples are 2.000, 3.000, 4.000, 5.000, 6.000, 7.000, 8.000, 10.000, 15.000, 20.000, 30.000, 40.000 and mixtures thereof.

Additionally, at least one of the above mentioned polypeptides may be linked to at least one different neutral amino acid residue, other peptides or other substances, such as a substance which cleans the injured surfaces, provides antioxidants, modulates apoptosis, promotes healing, inhibits fibrogenesis and tumour growth, controls bleeding, inhibits inflammation, increases stability or protects against infection. Examples are antimicrobial agents, antiinflammatory agents, cleaning agents, antioxidants, apoptosis modulators, healing agents, fibrogenesis inhibitors, antitumor agents and antibleeding agents.

Accordingly the polypeptides may be modified by amidation, esterification, acylation, acetylation, PEGylation or alkylation.

The above mentioned network may also comprise a pharmaceutical acceptable diluent or buffer.

“Pharmaceutically acceptable carrier” means a non-toxic substance that does not interfered with the effectiveness of the surface protection activity of the macromolecules, such as polypeptides. Such acceptable buffers or diluents are well-known in the art (see Remington's Pharmaceutical Sciences 18^(th) edition, A. R Gennaro, Ed., Mack Publishing Company (1990).

The term “buffer” is intended to mean an aqueous solution containing an acid-base mixture with the purpose of stabilising pH. Examples of buffers are Trizma, Bicine, Tricine, MOPS, MOPSO, MOBS, Tris, Hepes, HEPBS, MES, phosphate, carbonate, acetate, citrate, glycolate, lactate, borate, ACES, ADA, tartrate, AMP, AMPD, AMPSO, BES, CABS, cacodylate, CHES, DIPSO, EPPS, ethanolamine, glycine, HEPPSO, imidazole, imidazolelactic acid, PIPES, SSC, SSPE, POPSO, TAPS, TABS, TAPSO, TES, tricine.

The term “diluent” is intended to mean an aqueous or non-aqueous solution with the purpose of diluting the peptide in the pharmaceutical preparation. The diluent may be one or more of saline, water, polyethylene glycol, propylene glycol, ethanol or oils (such as safflower oil, corn oil, peanut oil, cottonseed oil or sesame oil).

The invented network may also comprises one or more therapeutic agent such as an antimicrobial, antiinflammatory agent, substances which cleans the injuried surfaces, provides antioxidants, modulates apoptosis, promotes healing, inhibits inhibits fibrogenesis and tumour growth or controls bleeding.

Examples of therapeutic agents are penicillins, ephalosporins, carbacephems, tetracyclines, macrolides, iodine, silver, copper, clorhexidine, acetylsalicylic acid and examples of cleaning substances are proteolytic enzymes.

Examples of agents having antioxidant activity are various vitamins, glutathione, folic acid, curcumin, resveratrol, epigallocathechin, anthocyanidins and numerous other agents.

Examples of agents which modulates apoptosis, inhibits fibrogenesis and tumour growth are glucocorticosteroids, insulin, dexamethasone, carotenoids, linoleic and conjugated-linoleic acids, melatonin, isothiocyanates, shikonin, solamargine, perifosine, deoxynivalenol, carboxyamido-triazole (CAI), histone deacetylase inhibitors and numerous other agents.

Examples of agents which promotes healing are various growth factors, insulin, vitamin E, retinoic acid, herbal components and numerous other agents and examples of agents which controls bleeding are norepinephrine, gelatin, collagen, oxidized cellulose and numerous other agents.

The above mentioned polypeptide can be synthesised by standard chemical methods including synthesis by automated procedure. In general, peptide analogues are synthesised based on the standard solid-phase Fmoc protection strategy with HATU (N-[DIMETHYLAMINO-1H-1.2.3.-TRIAZOLO[4,5-B]PYRIDIN-1-YLMETHYLELE]-N-METHYLMETHANAMINIUM HEXAFLUOROPHOSPHATE N-OXIDE) as the coupling agent or other coupling agents such as HOAt-1-HYDROXY-7-AZABENZOTRIAZOLE. The peptide is cleaved from the solid-phase resin with trifluoroacetic acid containing appropriate scavengers, which also protects side chain functional groups. Crude peptide is further purified using preparative reversed-phase chromatography. Other purification methods, such as partition chromatography, gel filtration, gel electrophoresis, or ion-exchange chromatography may be used. Other synthesis techniques, known in the art, such as the tBoc protection strategy, or use of different coupling reagents or the like can be employed to produce equivalent peptides.

An Applicator or Kit of the Invention

Additionally, the invention relates to an applicator comprising a cationic macromolecular substance and a pharmaceutically acceptable carrier, an anionic macromolecular substance and a pharmaceutically acceptable carrier, said cationic and anionic macromolecular substances being separated from each other by a separator. In embodiment, the applicator comprises a cationic polypeptide and a pharmaceutically acceptable carrier, an anionic polypeptide and a pharmaceutically acceptable carrier, said cationic and anionic polypeptides being separated from each other by a separator. The polypeptides being defined above and the solution is a pharmaceutically acceptable solution as defined above.

The applicator may be syringes, one or two component sprays, nebulators, plasters, catheters, adhesives, implants and bandages.

The separator separating the anionic and the cationic polypeptide prior to that they are applied to an injured tissue may be any separator as long as it is non-toxic and does not influence the effect of the polypeptides. The separator may be biodegradable. The main function of a separating layer between the two polypeptide solutions is to wash out all of the cationic peptide before administration of the polyanionic one and to avoid precipitation already in the applicator. It may comprise distilled water or any other suitable buffer. The separator may be a gelled state of the aqueous solution. Additionally the separator may be a membrane or any polymeric material, such as a polymer film.

Additionally, the applicator may comprise one or more therapeutic agents, such as those defined above. The agents, being (separated from the two polypeptides or) mixed with one or both of the polypeptides.

The therapeutic agent may be selected from the group consisting of penicillin, cephalosporin, carbacephems, tetracyclines, macrolides, iodine, silver, copper, clorhexidine and antiinflammatory agents such as acetylsalicylic acid.

Additionally the invention relates to a kit comprising a cationic macromolecular substance and a pharmaceutically acceptable carrier, an anionic macromolecular substance and a pharmaceutically acceptable carrier, and means for administering said macromolecular substances. In an embodiment, the kit comprises a cationic polypeptide and a pharmaceutically acceptable carrier, an anionic polypeptide and a pharmaceutically acceptable carrier, and means for administering said cationic and anionic polypeptides. The polypeptides being as defined above.

The means may be selected from the group consisting of syringes, sprays, plasters, catheter, adhesives, implant and bandages.

Additionally the kit may comprise one or more therapeutic agent such as antimicrobial and antiinflammatory agents. Other suitable therapeutic agents are those defined above. The therapeutic agent is selected from the group consisting of penicillin, cephalosporin, carbacephems, tetracyclines, macrolides, iodine, silver, copper, clorhexidine and acetylsalicylic acid.

The therapeutic agent in the applicator or kit described above may be separated from the two polypeptides or mixed with one or both of the polypeptides.

The applicator and/or the kit as described above may be used in therapy, such as in medicine, veterinary and horticulture.

Finally the invention relates to a method of treating a mammal having an injury, comprising use of the applicator and/or the kit as described above, creating the disclosed network. Examples of areas in which the invention can be useful includes ophtalmic bulb injuries and infections, nasal wounds, injuries and infections, skin injuries and infections, sun burns, thermic skin injuries/burns, bed sores, chronic leg ulcers, vaginal wounds, urinary bladder inflammation, oesophageal and stomach ulcers, inflammation and ulcers of the intestine, inflammations and serosal injuries of joints, cut surfaces or injuries to solid organs such as lung, liver and spleen, bone injuries, peritoneal defects and inflammation.

EXAMPLES

The invention will now be further described and illustrated by reference to the following examples. It should be noted, however, that these examples should not be considered as limiting the invention in any way.

Example 1 Adhesion Prevention.

A reproducible and standardized rat and rabbit model was adopted. Forty eight female MRI mice weighing about 25-30 g were used to induce the adhesions and forty two for further tests. The animals were kept under standardized conditions and had free access to pellet and tap water. Anesthesia was induced by ketamine 150 mg/kg (Ketalar, Parke Davis) and zylazine 7.5 mg/kg (Rompun, Bayer Sverige AB) intramuscular injection. After disinfection, a 25 mm long midline laparotomy was performed. Both peritoneal surfaces of the lateral abdominal wall were exposed, and 2×15 mm long sharp incisions were performed at the same distance from the midline, including the muscles. The wounds were immediately closed with 2×4 single sutures at equal distances by using 5.0 polypropylene (Prolene, Ethicon, Johnson & Johnson). The midline laparotomy was closed in two layers with a continuous 5.0 polypropylene suture. At the evaluation time an overdose of anesthetic was administered, the abdomen was totally opened through a U-shaped incision with its base to the right. The lengths of the adhesions were measured on both sides using a metal caliper, and data was expressed as percent wounds covered by adhesions.

Aqueous solutions of 0.5% poly-L-glutamate, and poly-L-lysine were freshly made on the day of the experiment and stored in refrigator until used. FITZ-labeled polylysine was mixed with polylysine in a proportion of 1:10 (wt). All chemicals and cell culture substrates were purchased from Sigma-Aldrich, St Louis, USA; fluorescent microparticles (Nile Blue Labeled) were bought from Microparticles GmbH., (Berlin, Germany).

The animals were divided randomly into 4 groups based on the treatment and the evaluation time. The control groups were intraperitoneally injected with 2 ml physio-logic sodium chlorine solution. Two treatment groups received 1 ml poly-L-lysine solution and 5 min later 1 ml poly-L-glutamate solution. One of the control and treatment groups (2×14 animals) was sacrificed one week after surgery and the lengths of the adhesions were calculated. The remaining two groups (2×10 animals) were kept for four weeks before they underwent the evaluation process. The Kruskal Wallis test was used to determine the difference in adhesion amount among the different treated groups and the Mann Whitney U test was used to compare the individual groups.

A significant decrease in adhesion development was detected both one week and one month after the peritoneal challenge (**p≦0.001) compared to the corresponding controls (Mann-Whitney U test). A marked (22%) though not significant (p=0.235) decrease was obtained after one month between the control groups, while there were no difference between the treated groups by that time.

No adhesions were found which were related to a heavy compound deposit in different locations from the wound itself. After 24 h, the animals that had been given both poly-L-lysine and poly-L-glutamate exhibited a massive protecting layer over the periotoneal wound, and thin film at the rest of peritoneal surface. However the FITZ-labeled compound was only visible in the wound one day later and was detectable both over and inside the wound. The deposit was gradually rebuilt until the end of the 6 day observation period.

Example 2 Phagocytosis and Particle Ingestion Index.

The time course of the phagocyte function was tested in vitro on peritoneal resident macrophages from mice after 0.5 h, 1 h, 2 h, 3 h, 4 h, 5 h, 6 h, 8 h, 10 h, 12 h, 16 h, and 24 h incubation with poly-L-lysine+poly-L-glutamate (40 μg/m1) and/or fluorescent particles (1 μm). Macrophage samples were taken by abdominal lavage with 10 ml ice cold DMEM-solution. The samples in medium were immediately centrifuged at 1200 rpm for 10 min. The cells were resuspended in DMEM containing 10% FBS and penicillin/streptomycin and then plated on 48 wells cell culture plates; 5×10⁵ cells in each well. After 1.5 h non-adherent cells were washed away, particles (100/cell) together with test drugs (poly-L-lysine+poly-L-glutamate) were added in a dose of 40 μg/ml to 12×5 wells, and particles only were added to the remaining 12×5 wells. Moreover negative controls were performed at each time point. The cells were incubated (37° C., 5% CO₂) and detached and fixed at the evaluation time by using 250 μl 5 mM EDTA and an equal volume of 2% paraformaldehyde. FACS analysis (FACScan, Becton Dickinson, San Jose, Calif.) was made, when cell size (forward scatter, FSC), granularity (side scatter, SSC) and fluorescence intensity (in FL3 channels) were recorded of 1.5×10⁴ cells in each measurement. In manually defined gates the ratio phagocyting cells/total macrophages was expressed in percent as mean of data from five wells at each time and treatment group (control and poly-L-lysine+poly-L-glutamate).

The non-treated cells incorporated more particles. Thus, the maximum plateau (median) level of their fluorescence intensity (FL3) and SSC was set as 100%. All measurements were expressed as the median percentage of the plateau level and termed particle ingestion index, since it refers to the amount of particles ingested. The Mann Whitney U test was used to check the plateau of phagocytosis and the Wilcoxon Signed Ranks test was used to test the difference in the phagocytosis and particle ingestion index between the treatment pairs (control and poly-L-lysine+poly-L-glutamate, respectively). While the phagocytosis index of the non-treated macrophages reached the plateau of phagocytosis about 5 h (the difference between 4 and 5 h decreased below the insignificant level, p=1), the treated population required 8 h for the same effect. (The difference between 8 and 10 h was insignificant, p=0.058). A low but significant (p=0.043) difference was obtained in the phagocytosis index after 24 h (97.3% and 94.3%, respectively). The time course for the ingestion index, which refers to the number of particles phagocytosed by macrophages became significant between 1 and 2 h (p=0.008). The control cell population reached the plateau between 16 and 24 h (insignificant difference between the index at 12 and 24 h (p=0.841) while the treated cell population did not reach the plateau at all during the first 24 h studied. Furthermore, the number of ingested particles were significantly lower in the treated group at all times (p=0.043). Flow cytometry verified that macrophages phagocyte the test compound particles, which resulted in significant cell growth and large phagocytic vacuoles.

Example 3 Transmission Electron Microscopy.

Peritoneal macrophages were harvested from two healthy non-treated animals as described above and plated on cell culture plates (Thermanox, Naperville, Ill., USA). The cells were washed away after 1.5 h and poly-L-lysine+poly-L-glutamate (40 μg/ml) in supplemented DMEM solution were added in sequence followed by a 24 h incubation. The incubation medium was removed and the cells were fixed in 2.5% phosphate buffered glutaraldehyde was followed by rinsing in Milloning's phosphate solution. Samples were postfixed in 1% osmium tetroxide and subsequently dehydrated with graded series of ethanol, which was followed by embedding in Araldite 502 kit. Vertical sections were obtained with a diamond knife and stained with uranyl acetate and lead citrate in a LKB Ultrastainer. Samples were examined in a JEOL 1200 EX transmission electron microscope (TEM). Electron microscopy verified that macrophages phagocyte the test compound particles, resulted in significant cell growth, and large phagocytic vacuoles.

Example 4 Scanning Electron Microscopy.

Peritoneal swabs and wounds were taken from eight treated (4) and non-treated (4) animals after one and seven days of surgery and cell cultures were conducted as above. The samples were fixed in 2.5% phosphate buffered glutaraldehyde at room temperature and then post-fixed in 1% OsO₄. The samples were dehydrated in acetone, critical point dried and sputter-coated with gold before being studied in a LEO 420 electron microscope. SEM data showed that mesothelial cells covered the compound surface from the first day.

Example 5 Histology.

Eight animals were opened and then injected intra-peritoneally with poly-L-lysine+poly-L-glutamate. At the postoperative first, second, third, and sixth days, two animals were sacrificed and the wounds were excised. They were rapidly frozen and embedded, and the block obtained was immediately cut into slices of 7 μm. The slices were allowed to dry in dark for 30 min at room temperature and were then stained with 100 μg/l 4′6′-diamino-2-phenylindole hydrochloride (DAPI) solution for 10 min. Fluorescent microscopy was performed with both a FITZ and a DAPI filter, and images were digitally merged (OpenLab, Improvosion). Macro photo was made about the excised wounds by using trans-illumination, mixed ambient room light, and UV illumination.

The histological studies showed that the added material was present in the wound from the first day. Furthermore, more and more cells were detected for each day until the matrix was completely rebuilt.

Example 6 Biodegradation.

Healthy non-operated animals were treated intra-peritoneally as in Example 1 and sacrificed after two months.

No visible remains of poly-L-lysine and poly-L-glutamate could be detected. The biodegradability is supported by findings that at one month's follow up the same results were obtained by using a double dose of poly-L-lysine+poly-L-glutamate, although that caused some additional adhesions related to the compound at evaluation on the 7^(th) day.

Example 7 Biodegradation.

Aqueous solutions of 1% and 2% lysozyme, poly-L-glutamate, poly-L-lysine, and poly-L-glutamate, and 0.25% of hyaluronic acid were freshly made. Solutions of lysozyme, polyglutamate, lysozyme+polyglutamate and polylysine+polyglutamate were then administered to animals as in Example 1.

The extent of abdominal adhesions one week after surgery significantly decreased in the four treated groups (p≦0.001) as compared to controls. However, no significant change in response was obtained with hyaluronic acid (p=0.264). The combinations poly-L-lysine/lysozyme seemed to result in an insoluble product.

Example 8 Effect of Poly-L-lysine Alone.

An aqueous solution of 0.5% poly-L-lysine was freshly made and administered to animals as in Example 1. Such an administration of poly-L-lysine alone resulted in convulsions and death within 30 min, i.e. before they woke up from the anesthesia. The symptoms seemed to be related to the effect of opening calcium channels, plasma Ca⁺⁺ levels being rapidly decreased.

Outlay of the Experimental Procedure

a. Standard thermic injuries were produced on the two sides of the back of ten mice. One wound was treated with the composition, the other served as control. Reduced rate of infection, faster healing and less sequelae were seen in the treated wounds. b. One cm long incisions were done on each side of the back of ten rats. One incision was filled with the composition, the other served as control. Uneventful and faster healing was observed of the treated wound. c. Standard incisions were done in both the liver and spleen of ten rats. Additional ten rats served as controls. The amount of bleading was significantly reduced in the treated animals. The treatment glued together the defect, which resulted in a faster healing and less sequelae. d. Colonic mucosa inflammation and wounds were induced in rats by several methods such as acetic acid infusion, methotrexate and dextran sulphate. The inflammatory surfaces and wounds were “painted” with the composition. Reduced inflammation and enhanced healing was observed. e. Human nasal mucosa wounds and infections were treated with the composition. A fast cleansing of the wounds and healing was observed. f. Human bed sores were treated by the composition. A fast cleansing of the infected and necrotic surfaces was observed. The treatment was repeated over a longer period of time. g. Human chronic leg ulcers were treated by the composition, A fast cleansing of the infected and necrotic surfaces was observed. The treatment was repeated over a longer period of time.

Example 9 Effect of Concentration.

Concentrations of polylysine and polyglutamate between 0.1 wt %-0.5 wt % were used to form a barrier network. FIG. 4 shows the anti-adhesion effects in rabbits of 0.5%, 0.25%, and 0.1% concentrations. The adhesion percentage was found to increase with decreasing concentration. The upper concentration was found to be limited by the practicality of mixing and spraying. A high concentration resulted in higher viscosity. As the viscosity is increased, the solutions became more difficult to mix and spray. The toxicity of the chosen macromolecule also affected the concentration range in which the macromolecule can be used.

Example 10 Variation of Net Charge and Charge Density.

Variation of charge density and net charge was studied by using a number of different cationic macromolecules. α-polylysine (α PL), ε-polylysine (ε-PL), lactoferrin, lysozyme, and polyarginine were studied. A barrier network was formed for all of the different polypeptides and proteins. As shown in FIG. 5, all the polypeptides and proteins formed a barrier network that protected the injured surfaces in the animals, and prevented the formation of adhesions. 

1. A biodegradable network for covering a wound, comprising at least one macromolecular substance having a positive charge and at least one second macromolecular substance having a negative charge.
 2. The network according to claim 1, wherein the net charge per macromolecule used for the formation of the network is at least 3 elementary charges.
 3. The network according to claim 1, wherein the charge density of each of the two macromolecules used for the formation of the network is at least 1 elementary charge per 3 times the Debye length.
 4. The network according to claim 3, wherein the Debye length of the respective macromolecules in the medium used for administration is about 1 nm.
 5. The network according to claim 1, wherein the charge density of the macromolecules used for the formation of the network is at least 10% calculated as the fraction of charged monomers in relation to the total amount of monomers forming the network.
 6. The network according to claim 1, wherein the network is insoluble in the medium used for administration.
 7. The network according to claim 1, wherein the macromolecular substances are polypeptides.
 8. The network according to claim 7, wherein the polypeptides comprise a combination of charged amino acids, and neutral amino acids.
 9. The network according to claim 8, wherein the charged amino acids comprise cationic amino acids.
 10. The network according to claim 9, wherein the cationic amino acids comprise lysine, arginine, or histidine.
 11. The network according to claim 8, wherein the charged amino acids comprise anionic amino acids.
 12. The network according to claim 11, wherein the anionic amino acids comprise aspartate, glutamate, asparagine, or glutamine.
 13. The network according to claim 8, wherein the neutral amino acids comprise glycine, alanine, valine, leucine, isoleucine, tyrosine, tryptophan, phenylalanine, proline, cysteine, or methionine.
 14. The network according to claim 1, wherein the positively charged macromolecular substance is a cationic polypeptide consisting of 10-100 mol % of cationic amino acids and 0-90 mol % of the neutral amino acids, and the negatively charged macromolecular substance is an anionic polypeptide consisting of 10-100 mol % of anionic amino acids and 0-90 mol % of neutral amino acids.
 15. The network according to claim 7, wherein the cationic polypeptides are 100% composed by a combination of cationic charged amino acids, and the anionic polypeptides are composed by a combination of 100% anionic amino acids.
 16. The network according to claim 7, wherein the polypeptides are homopolypeptides consisting of only one type of monomer, respectively.
 17. The network according to claim 11, wherein the homopolypeptides consists of the aminoacids lysine and glutamate.
 18. The network according to claim 1, wherein at least one of the macromolecular substances is a protein.
 19. The network according to claim 18, wherein one of the cationic macromolecules is the protein lysozyme and the anionic macromolecule is polyglutamate.
 20. A method for covering a wound comprising subsequent steps of: a) applying a solution of a macromolecular substance having a positive charge to the wound, b) applying a solution of a macromolecular substance having a negative charge to the wound, and c) letting the first substance and the second substance form an insoluble network on top of the wound.
 21. A biodegradable barrier network, comprising: a) a cationic polypeptide, b) an anionic polypeptide and c) a pharmaceutically acceptable carrier. 